WO2017010119A1 - Technique pour normaliser une image de scintigraphie - Google Patents

Technique pour normaliser une image de scintigraphie Download PDF

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Publication number
WO2017010119A1
WO2017010119A1 PCT/JP2016/056550 JP2016056550W WO2017010119A1 WO 2017010119 A1 WO2017010119 A1 WO 2017010119A1 JP 2016056550 W JP2016056550 W JP 2016056550W WO 2017010119 A1 WO2017010119 A1 WO 2017010119A1
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Prior art keywords
pixel value
value
values
pixel
image data
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PCT/JP2016/056550
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English (en)
Japanese (ja)
Inventor
和宏 西川
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日本メジフィジックス株式会社
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Application filed by 日本メジフィジックス株式会社 filed Critical 日本メジフィジックス株式会社
Priority to CN201680025193.3A priority Critical patent/CN107533141A/zh
Priority to JP2017528294A priority patent/JP6745268B2/ja
Priority to US15/569,442 priority patent/US10366479B2/en
Priority to EP16824100.8A priority patent/EP3279697A4/fr
Priority to KR1020177027351A priority patent/KR20180030460A/ko
Publication of WO2017010119A1 publication Critical patent/WO2017010119A1/fr
Priority to HK18102758.8A priority patent/HK1243492A1/zh

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    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T5/00—Image enhancement or restoration
    • G06T5/40—Image enhancement or restoration using histogram techniques
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G01T1/164—Scintigraphy
    • G01T1/1641—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras
    • G01T1/1647—Processing of scintigraphic data
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G01T1/164—Scintigraphy
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/10—Image acquisition modality
    • G06T2207/10116—X-ray image
    • G06T2207/10128—Scintigraphy
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/30—Subject of image; Context of image processing
    • G06T2207/30004—Biomedical image processing
    • G06T2207/30008—Bone

Definitions

  • the present invention relates to normalizing scintigraphic images obtained by nuclear medicine techniques.
  • Scintigraphy used in nuclear medicine examination is a kind of nuclear medicine imaging technology.
  • a radiopharmaceutical is administered into the body, and gamma rays emitted due to the decay of the nuclide are captured by a SPECT device or the like and imaged.
  • scintigraphy normalization of pixel values, that is, conversion of pixel values into values comparable to other images is performed for the purpose of performing follow-up observation, image comparison, and the like.
  • the normalization method includes a manual method in which an operator visually adjusts the level and a method in which normalization is performed automatically.
  • the manual method has an advantage that it is not necessary to use a special program, it has a disadvantage that the result depends on the skill level of the operator. For example, in the method of visually adjusting the level, the result is easily influenced by the operator's sense, and as a result, variations are likely to occur. Also, there is a method of taking the ROI in the thoracic vertebra and normalizing it using the maximum value, but this method cannot be used when the abnormal accumulation exists in the created ROI.
  • Patent Document 1 and Non-Patent Document 1 listed below disclose a method for semi-automatically determining a normalization reference value for a bone scintigraphic image, which is one of the applied fields of scintigraphy.
  • the multiple scoring method disclosed in Non-Patent Document 2 below is used to analyze a histogram of a bone scintigraphic image and to detect pixel values corresponding to abnormal accumulation of radiopharmaceuticals and pixels corresponding to normal accumulation. Determining a boundary value with the value and normalizing the bone scintigraphic image with respect to the boundary value is described.
  • Patent Document 1 and Non-Patent Document 1 sometimes lack stability in the result of normalization. Therefore, the inventor of the present application has sought to develop a technique for performing normalization more stably than these conventional techniques, and has come to make the present invention.
  • Patent Document 1 and Non-Patent Document 1 are characterized in that a reference value for normalization is determined depending on the range and value of a region having a high pixel value. That is, the reference value is determined based on a region where abnormal accumulation of radiopharmaceuticals occurs.
  • the inventor of the present application considered that this feature is a cause of lack of stability.
  • the inventors of the present application have found that the stability of normalization can be improved by determining a reference value for normalization based on the normal accumulation region.
  • An example of a preferred embodiment of the present invention is the following method.
  • This method is for normalizing bone scintigraphic images obtained by nuclear medicine techniques, Reading image data representing the bone scintigraphy image; Creating a pixel value histogram of the image data; Setting a plurality of threshold values for pixel values based on the pixel value histogram; Calculating a pixel value average value for each of the set threshold values; Arranging the calculated pixel value average values in order of increasing values; Determining a reference value for normalizing the image data based on at least part of the set of pixel value averages arranged in the order; Determining the reference value, Determining one straight line approximating a region having a small pixel value average value among the set of pixel value average values arranged in the order; Calculating the reference value based on the straight line; It is characterized by including.
  • determining one straight line removes several large pixel value average values from the set of pixel value average values, and calculates an approximate straight line that approximates the remaining portion. Further, the method may include calculating a correlation coefficient between the approximate line and a set of pixel value average values used for calculating the approximate line.
  • the method changes the number of average pixel values to be removed, calculates the approximate line and the correlation coefficient in each case, and based on the calculated values of the plurality of correlation coefficients Determining one of the straight lines.
  • the region where the pixel value average value is small may be determined based on a change rate of a set of pixel value average values arranged in the order.
  • the reference value may be determined based on an intercept of the straight line.
  • the method may further include normalizing the image data based on the reference value and displaying the normalized image data.
  • setting a plurality of threshold values related to pixel values based on the pixel value histogram may be performed using a multiple threshold method.
  • a system comprising processing means and storage means, wherein the storage means stores program instructions, and the program instructions are executed by the processing means, whereby the system includes ,
  • a system configured to perform any of the above methods is included.
  • Preferred embodiments of the present invention include a computer program comprising program instructions configured to cause the system to perform any of the methods by being executed by a processing means of the system.
  • Preferred embodiments of the present invention include the following system.
  • This system is for normalizing bone scintigraphic images obtained by nuclear medicine techniques, Means for reading image data representing the bone scintigraphic image; Means for creating a pixel value histogram of the image data; Means for setting a plurality of threshold values relating to pixel values based on the pixel value histogram; Means for calculating an average pixel value for each of the plurality of threshold values set; Means for arranging the calculated pixel value average values in order of increasing values; Means for determining a reference value for normalizing the image data based on at least part of the set of pixel value averages arranged in the order; And the means for determining the reference value comprises: Means for determining one straight line approximating a region having a small pixel value average value among the set of pixel value average values arranged in the order; Means for calculating the reference value based on the straight line; It is characterized by providing.
  • FIG. 2 is a diagram for describing a main configuration of a system 100, which is an example of hardware that can execute various processes disclosed in the present specification. It is a flowchart for demonstrating the image normalization process disclosed by this specification. It is an example of the pixel value histogram of a bone scintigraphy image. It is the example which displayed the sorted pixel value average value in the graph. It is a flowchart for demonstrating the example of the process which determines the straight line which approximates the data of the sorted pixel value average value.
  • FIG. 6A is a display example of image data before normalization
  • FIG. 6B is a display example of image data after normalization.
  • FIG. 7A is a diagram for correlating a manual normalization value by a nuclear medicine specialist and an automatic normalization value according to the prior art for a certain bone scintigraphy image
  • FIG. It is a figure for seeing the correlation of the manual normalization value by a nuclear medicine specialist and the automatic normalization value by this invention.
  • FIG. 1 is a diagram for explaining a main configuration of a system 100, which is an example of hardware capable of executing various processes disclosed in the present specification.
  • the system 100 is similar to a general computer in hardware, and includes a CPU 102, a main storage device 104, a mass storage device 106, a display interface 107, a peripheral device interface 108, a network.
  • An interface 109 or the like can be provided.
  • a high-speed RAM Random Access Memory
  • an inexpensive and large-capacity hard disk or SSD can be used as the large-capacity storage device 106. it can.
  • a display for displaying information can be connected to the system 100, which is connected via a display interface 107.
  • a user interface such as a keyboard, a mouse, and a touch panel can be connected to the system 100, and this is connected via the peripheral device interface 108.
  • the network interface 109 can be used to connect to another computer or the Internet via a network.
  • the mass storage device 106 may store an operating system (OS) 110, an image normalization program 120 for providing characteristic processing disclosed in the present specification, and the like.
  • OS operating system
  • image normalization program 120 for providing characteristic processing disclosed in the present specification, and the like.
  • the most basic functions of the system 100 are provided by the OS 110 being executed by the CPU 102.
  • the characteristic processing disclosed in this specification is provided by causing the CPU 102 to execute at least a part of a program instruction group included in the image normalization program 120.
  • there are various implementation forms of the program and all of these variations are included in the scope of the invention disclosed in the present application.
  • the mass storage device 106 further includes bone scintigraphy image data 130 to be subjected to normalization processing by the image normalization program 120, normalization reference value data 132 generated as a result of processing by the image normalization program 120, Image data 134 obtained by normalizing the image data 130 can also be stored.
  • the system 100 can have the same configuration as an apparatus included in a normal computer system, such as a power supply or a cooling device.
  • the implementation form of the computer system includes storage device distribution / redundancy and virtualization, use of multiple CPUs, CPU virtualization, use of a processor specialized for specific processing such as DSP, and implementation of specific processing in hardware.
  • Various forms using various techniques, such as combining, are known.
  • the invention disclosed in the present application may be mounted on any form of computer system, and the scope thereof is not limited by the form of the computer system.
  • the technical idea disclosed in this specification is generally (1) executed by a processing unit to cause an apparatus or a system including the processing unit to perform various processes described in this specification. (2) an operation method of an apparatus or a system realized by the processing means executing the program, and (3) the program and the program.
  • the present invention can be embodied as an apparatus or system provided with processing means. As described above, some software processing may be implemented as hardware.
  • the bone scintigraphic image data 130 may be data transferred from an external device to the system 100 via the peripheral device interface 108 or the network interface 109, for example.
  • the data 132 and 134 may be formed through execution of the program 120 by the CPU 102. Further, depending on the implementation form of the program 120 and the OS 110, the data 132 and / or 134 may not be stored in the mass storage device 106 but may be stored only in the main storage device 104. It should be noted that the scope of the invention disclosed in the present application is not limited by the presence or absence of the data 130-134.
  • the bone scintigraphic image data 130 can be, for example, two-dimensional image data obtained by a SPECT examination performed using a radiopharmaceutical adsorbed on a hydroxyapatite crystal that is a basic composition of bone mineral. More specifically, for example, 99m Tc-HMDP as a radiopharmaceutical is intravenously administered to a subject, radiation emitted from the body is detected by a SPECT device, and two-dimensional image data formed based on the radiation count value Can be.
  • each pixel value of the pixels constituting these images has a value corresponding to the radioactivity count value, that is, each pixel value represents the intensity of radioactivity.
  • the image data 130 may be time-series two-dimensional data, three-dimensional image data, or time-series three-dimensional data.
  • FIG. 2 is a flowchart for explaining the image normalization process 200 disclosed in this specification.
  • the process introduced in this flowchart can be, for example, a process performed by the system 100 when a program command of the image normalization program 120 is executed by the CPU 102.
  • Step 202 indicates the start of processing.
  • the bone scintigraphic image data 130 to be processed in this embodiment is read.
  • the CPU 102 copies at least a part of the image data 130 from the mass storage device 106 to the main storage device 104 in accordance with an instruction of a program instruction group included in the image normalization program 120.
  • the bone scintigraphy image data 130 can be read by a dedicated reading device stored in a storage medium and taken into the system 100 via the peripheral device interface 108.
  • the bone scintigraphic image data 130 may be captured via the network interface 109 as a data signal superimposed on a carrier wave.
  • the captured bone scintigraphic image data 130 may be temporarily stored in the large-capacity storage device 106 and copied to the main storage device 104, or may be stored directly in the main storage device 104 and continue as it is. You may use for a process.
  • a histogram of pixel values of the image data 130 is created.
  • the generated histogram data may be stored in the main storage device 104 or the large-capacity storage device 106 for use in the processing of the subsequent steps or for display.
  • FIG. 3 shows an example in which a pixel value histogram created from certain actual bone scintigraphic image data is displayed.
  • the horizontal axis of the histogram is the class value, which is a value related to the pixel value.
  • the vertical axis is frequency.
  • a plurality of threshold values relating to pixel values are set using the pixel value histogram created in step 206.
  • a multiple threshold method is used to set multiple thresholds. Specifically, for example, this is performed as follows. First, a plurality of class values are obtained such that the area under the histogram from the class value zero to a certain class value is a predetermined ratio of the total area under the histogram. For example, a class value A1 that divides the entire area under the histogram into, for example, 1% is obtained. Next, the division ratio is sequentially increased from 1% to 100%, for example, in increments of 1%, for example, and class values A1, A2,. Then, the obtained class value is set as a threshold value.
  • a method of determining a plurality of threshold values and extracting specific pixels in this way is called a multiple threshold method.
  • the frequency will fluctuate greatly with a slight difference in the class value, so the difference between the class value A i and the class value A i + 1 will be very small.
  • the frequency does not change much even if the class value changes, and the frequency itself is small, so the difference between the values of A i and A i + 1 will be relatively large.
  • the pixel value average value is calculated for each of the plurality of threshold values determined in step 208.
  • step 212 a pixel group having a pixel value equal to or greater than a threshold value (for example, A i ) at the current loop position is extracted from the image data 130.
  • Step 214 is an optional process and will be described later.
  • step 216 the average value of the pixel values of the pixel group extracted in step 212 is calculated.
  • Step 212 and step 216 are performed for all of the plurality of threshold values determined in step 208, and the corresponding pixel value average value is calculated.
  • the calculation result may be stored in the main storage device 104 or the large-capacity storage device 106 for use in processing of subsequent steps, display, or the like.
  • step 214 described below may be executed between step 212 and step 216.
  • step 214 for the pixel group extracted in step 212, adjacent pixels are connected to form a cluster. Then, the number of pixels of each formed cluster is examined, and pixels included in the cluster in which the number of pixels does not satisfy a predetermined condition are specified.
  • step 214 pixels included in a cluster that does not satisfy a predetermined condition in the calculation of the pixel value average value in step 216 may be excluded from the calculation. As a specific example, for example, pixels included in a cluster having 10 or less pixels may be excluded from the pixel value average value calculation in step 216.
  • a process of excluding a pixel included in a cluster whose number of pixels is not within a predetermined range from the calculation of the pixel value average value may be performed.
  • step 220 the plurality of pixel value average values calculated in the loop represented by reference numerals 210 to 218 are arranged in the descending order. That is, sort processing is performed in descending order.
  • the sorted average pixel values may be displayed in a graph.
  • An example of a graph display is shown in FIG.
  • the value on the horizontal axis of this graph is a numerical value indicating the order of the sizes.
  • the point whose horizontal axis value is 1 in the graph has the largest pixel value average among all the data points. Indicates a value.
  • a point having a horizontal axis value of 10 in the graph indicates that the pixel value average value is the 10th largest value among all the data points.
  • the straight line 410 drawn in FIG. 4 will be described later in connection with step 514 in FIG.
  • step 222 one straight line approximating the sorted pixel value average value data that can be represented by a graph as shown in FIG. 4 is determined.
  • the straight line determined here becomes a basis for calculating a reference value for normalizing the image data 130 in the subsequent steps. What is important in step 222 is that an approximate straight line is determined using data in a region where the average pixel value is small.
  • the basic technical idea of the present invention is to determine a reference value for normalization based on data of a region representing normal accumulation in a scintigraphic image. The region representing normal accumulation in the graph of FIG. This is because the pixel value average value is a small region.
  • the method for obtaining an approximate line of a plurality of data points is known, but it is necessary to devise in order to automatically use an area having a small average pixel value as an area for obtaining an approximate line.
  • One preferred embodiment of the present invention solves this problem using an algorithm as illustrated in FIG.
  • FIG. 5 is an example of a process for determining one straight line approximating sorted pixel value average value data that can be represented by a graph as shown in FIG. 4, and the pixel value average value is small. It is a flowchart for demonstrating the example 500 of a process which determines an approximate straight line using an area
  • Step 502 indicates the start of processing.
  • Reference numerals 504 to 512 indicate a loop process, and each time the process returns to 506, the data range for calculating the approximate straight line is changed in step 508.
  • an approximate line is calculated using the data in the range set in step 506.
  • the approximate line obtained in step 508 and the data used for calculating the approximate line that is, set in step 506).
  • the correlation coefficient with the data in the range is calculated.
  • the setting of the approximate range in step 506 is performed as follows. First, when the process 500 first proceeds to 506, the entire data range is set as a range for calculating an approximate straight line. When the process 500 returns to 506, the range for calculating the approximate straight line is reset except for the data point having the largest pixel value average value. When the process 500 returns to 506 next time, the range for calculating the approximate straight line is reset except for the data point having the largest pixel value average value in the previous range.
  • the data range set when the process 500 first proceeds to 506 is represented by the value on the horizontal axis. 1-100.
  • the data range that is set when the process 500 returns to 506 next is 2-100 on the horizontal axis.
  • the data range set when the process 500 returns to 506 next is 3-100 on the horizontal axis.
  • steps 508 and 510 an approximate straight line and a correlation coefficient are calculated for each set range.
  • the data range that is set when the process 500 first proceeds to 506 does not necessarily include the data point with the largest pixel value average value. It should be noted that the pixel value average value need not necessarily include the smallest data point. Further, a lower limit value may be set for the number of data points included in the data range.
  • the data range set when the process 500 first proceeds to 506 may be a value on the horizontal axis, for example, 3-90, etc.
  • the data range set immediately before exiting may be 81-90, for example, on the horizontal axis.
  • a plurality of information on the set range, information on the corresponding straight line, and information on the corresponding correlation coefficient are calculated.
  • Such information may be stored in the main storage device 104 or the large-capacity storage device 106 for use in processing of subsequent steps, display, or the like.
  • one approximate line is determined based on the information calculated in the loops 504-512. In one example, in the loops 504 to 512, it may be determined that the straight line has the largest correlation coefficient.
  • a straight line 410 in FIG. 5 illustrates a straight line determined by this method.
  • the straight line on which the correlation coefficient first peaks may be the straight line determined in step 514.
  • the peak may be determined after applying an appropriate smoothing process.
  • a straight line corresponding to a second or third peak in another order may be a straight line determined in step 514.
  • the straight line at that time may be a straight line determined in step 514.
  • the data used as the basis for the calculation of the determined straight line is data in a region where the pixel value average value is small. That is, in the graph of FIG. 4, the data that is the basis for the calculation of the determined straight line is data in a region where the value on the horizontal axis is large.
  • Step 516 represents the end of the process.
  • a predetermined range may be determined as a range for calculating the approximate straight line.
  • a range of, for example, 30% -80% of the maximum value on the horizontal axis where the data point exists may be determined as a range for calculating the approximate straight line.
  • the rate of change between adjacent data points is obtained, and an approximate straight line is calculated at the point where the absolute value of the rate of change is below a predetermined threshold.
  • a predetermined threshold There is also a method of setting the lower limit of the range to be performed.
  • the absolute value of the rate of change is large in the region where the value on the horizontal axis is small, and gradually decreases as the value on the horizontal axis increases. Therefore, if the threshold value of the absolute value of the change rate is sufficiently small, it is possible to set the approximate range so that only the region where the pixel value average value is small is included.
  • step 224 a reference value for normalizing the data 130 is determined based on the approximate straight line determined in step 222.
  • this reference value is the value of the Y intercept of the approximate straight line determined in step 222. Therefore, in the case of the approximate line 410 illustrated in FIG. 4, this reference value is approximately 65.
  • the reference value is the maximum value on the vertical axis in the data range on which the approximate straight line is based.
  • the method for determining the reference value is not limited to these examples. However, in any case, it is necessary to determine a reference value based on the approximate straight line determined in step 222.
  • the determined reference value may be stored in the main storage device 104 or the large-capacity storage device 106 for use in processing of subsequent steps, display, or the like.
  • the bone scintigraphic image data 130 is normalized using the reference value determined in step 224.
  • how to use the reference value is not particularly limited, and various variations are conceivable.
  • the pixel value of each pixel of the bone scintigraphy image data 130 is normalized to, for example, 1-1024, and the reference value is a specific value (for example, 300) within the scale. It is good also as adjusting the whole value so that it becomes.
  • the normalized image data may be stored in the main storage device 104 or the mass storage device 106 for use in further processing, display, or the like.
  • step 228, the normalized image data is displayed. Display examples are shown in FIGS. 6A and 6B. 6A shows the image data 130 before normalization processing, and FIG. 6B shows the image data 130 normalized by the above processing. The reason why the detailed structure does not appear in these images is that the image data that can be used for the patent application is limited to binary. Originally, it is possible to display a high-definition image in a multi-value format using gray scale or color.

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Abstract

Le problème décrit par la présente invention est de perfectionner la stabilité de normalisation automatique d'une image de scintigraphie osseuse. La solution de l'invention porte sur un mode de réalisation préféré qui consiste à : générer un histogramme de valeurs de pixels pour des données d'image qui représentent une image de scintigraphie osseuse ; établir une pluralité de valeurs de seuil concernant les valeurs de pixels sur la base de l'histogramme de valeurs de pixels ; calculer des valeurs moyennes de valeurs de pixels par rapport à chaque valeur de la pluralité de valeurs de seuil définies ; agencer les valeurs moyennes de valeurs de pixels calculées par ordre de grandeur des valeurs ; et déterminer, sur la base d'au moins une partie du regroupement de valeurs moyennes de valeurs de pixel qui ont été agencées dans l'ordre, une valeur de référence pour normaliser les données d'image, la détermination de la valeur de référence comprenant la détermination d'une ligne qui s'approche d'une région dans laquelle les valeurs moyennes de valeurs de pixels sont faibles à partir du regroupement de valeurs moyennes de valeurs de pixels qui ont été disposées dans cet ordre, et calculer la valeur de référence sur la base de la ligne.
PCT/JP2016/056550 2015-07-14 2016-03-03 Technique pour normaliser une image de scintigraphie WO2017010119A1 (fr)

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CN201680025193.3A CN107533141A (zh) 2015-07-14 2016-03-03 闪烁扫描术图像的正规化技术
JP2017528294A JP6745268B2 (ja) 2015-07-14 2016-03-03 シンチグラフィー画像の正規化技術
US15/569,442 US10366479B2 (en) 2015-07-14 2016-03-03 Technique for normalizing scintigraphy image
EP16824100.8A EP3279697A4 (fr) 2015-07-14 2016-03-03 Technique pour normaliser une image de scintigraphie
KR1020177027351A KR20180030460A (ko) 2015-07-14 2016-03-03 신티그래피 화상의 정규화 기술
HK18102758.8A HK1243492A1 (zh) 2015-07-14 2018-02-27 閃爍掃描術圖像的正規化技術

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US10366479B2 (en) * 2015-07-14 2019-07-30 Nihon Medi-Physics Co. Ltd. Technique for normalizing scintigraphy image
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